|Publication number||US4527560 A|
|Application number||US 06/437,158|
|Publication date||Jul 9, 1985|
|Filing date||Oct 27, 1982|
|Priority date||Oct 27, 1982|
|Also published as||CA1222290A, CA1222290A1|
|Publication number||06437158, 437158, US 4527560 A, US 4527560A, US-A-4527560, US4527560 A, US4527560A|
|Inventors||Carl J. Masreliez|
|Original Assignee||Masreliez Carl J|
|Export Citation||BiBTeX, EndNote, RefMan|
|Patent Citations (4), Referenced by (45), Classifications (10), Legal Events (5)|
|External Links: USPTO, USPTO Assignment, Espacenet|
1. Technical Field
The present invention relates to a medical or dental probe which can deliver continuous heat to a tip, particularly to a narrow, pointed instrument tip.
2. Background Art
In dentistry, narrow, heated tips can be used in root canal therapy when filling the root system with heat-softened gutta-percha (natural rubber) or other substances. Also, a heated instrument is used to build wax replicas of teeth. These replicas are then used for castings via the lost-wax method. A similar method of wax casting is also used in the jewelry industry. In a medical application, a heated tip is often used to seal (cauterize) blood vessels. Many other medical applications are also apparent.
The conventional means for achieving a heated instrument tip today is to heat the tip externally, for example, by holding the tip in a flame or in contact with a resistive heater. The primary disadvantage of this approach is that the instrument tip cools off too rapidly, particularly if the tip is narrow. To achieve the desired degree of heating at the end of the tip, it is often necessary to heat the tip to glowing. This degree of heating increases the risk of accidental burns and tends to rapidly destroy the tip.
Heating of the tip by contact with a resistive heater sometimes involves contacting the tip between an open circuit so that current flows through the tip and thereby heats the tip. This method is disclosed in U.S. patent application Ser. No. 273,906 for a dental instrument heater. Alternatively, the instrument tip may be placed in contact with a resistive heating element so that heat is transferred to the tip by conduction. This method is similar to the common operation of a soldering iron.
A disadvantage of contacting the instrument tip across an open circuit is that sparking of the short circuit may cause "pitting" of the instrument. Also, of course, it is difficult to regulate the temperature of the tip, so the tip may be either overheated or not heated enough. Disadvantages of contacting a resistive heating element include the difficulty of conducting sufficient heat to the end of the instrument tip, particularly if the instrument is narrow. As the heat is conducted along the instrument tip, much of it is radiated and convected away to the surrounding atmosphere. Also, a relatively long time for both the heating and cooling cycles makes the conduction-resistive heater approach undesirable.
The present invention relates to a medical or dental probe with a self-heating tip and to methods for making these tips. The tip itself is a resistive heating element, thus making rapid heating of narrow and fine instrument tips easily accomplished without pitting. Furthermore, the instrument tip may supply nearly continuous heat through direct resistive heating rather than steadily varying heating through staged heating and cooling cycles. The tip may be properly designed to concentrate the heat at the tip by concentrating the current density in this vicinity.
In one embodiment, an electrically conductive core is surrounded by a nonconductive layer, such as common dielectric insulation. An outer resistive heating layer encircles the core and is electrically connected to the core at a leading end of the core. Current passing through the core and into the resistive layer causes the resistive layer to heat up. The outer resistive layer is preferably constructed so that its cross-sectional perimeter increases as the layer gets farther away from the leading end of the core. A resistive layer of this nature concentrates heating at the tip by increasing the current density at the tip. The tip may also be implemented by a resistive core surrounded by a conductive layer, or the core and outer layer could both be resistive, with the core and outer layer being electrically isolated except at the end.
A second preferred embodiment includes a conductive core on which an insulative layer is deposited by a suitable technique, such as, for example, vacuum depositing, spraying, or anodizing. An outer resistive layer is deposited around the insulation while being connected to the core at its end. Again, as in the first embodiment, the resistive layer is designed to concentrate heating of the resistive layer at the tip.
It is unnecessary that the tip be generally a frustum (i.e., a truncated cone), and instead it may be any desired shape, so long as a conductive element projects to a leading end, where a resistive element is connected to the conductive lead. The resistive element is usually fabricated so that when it heats up, the heat is concentrated at the leading end of the conductor lead. For example, a layered tip may be constructed.
Methods for making self-heating tips and dental probes are also disclosed.
FIG. 1 is an isometric view of a preferred embodiment of the inventive medical or dental probe.
FIG. 2 is a cross-sectional view of the tip/probe interface.
FIG. 3 is a typical longitudinal cross-section of an instrument tip of this invention.
FIG. 4 is a longitudinal cross-sectional view similar to FIG. 3 showing a second preferred embodiment of a tip of this invention.
FIG. 5 is a schematic block diagram of the electrical circuitry used to heat the tip.
As shown in FIG. 1, a probe 10 has a base 12 which functions as a handle for the probe 10 and which holds a tip 14, which will be described in more detail. With reference, also, to the schematic of FIG. 5, the rear end of the base 12 includes a step-down transformer 16 having its primary connected to a power cord 18 of the probe 10 to provide electrical power to the tip 14. Use of a transformer within the probe 10 allows the probe cord 18 to carry a relatively small current. The power for the tip 14 may thus be transferred through the cord 18 at a higher voltage and at a lower current so that the transformer 16 may convert this power into a lower voltage/higher current power source, as desired. Power is supplied through the cord 18 by a control unit 19 which is powered either from a wall outlet or by an internal battery. The control unit 19 has a panel on which is mounted an on/off switch 20 and a power control 21. The voltage and current requirements of the tip 14 will vary depending upon its size and desired temperature. However, in one operational embodiment, 10 watts of power are supplied to the tip 14.
The transformer 16 receives power through the probe cord 18 from a transformer driver 23 which may use power transistors or a conventional power amplifier. The driver 23 is capable of supplying sufficient power to heat the tip 14. The transformer driver 23 is energized by the output of an AND-gate 22. The AND-gate 22 receives the output of an oscillator 24, a one-shot 26 (periodically triggered by a second oscillator 28), and the output of an amplifier 30 controlled by an on/off switch 32. When the tip 14 is to be heated, the output of the amplifier 30' is high, as explained hereinafter. Thus, gate 22 is controlled by oscillator 24 and one-shot 26. Oscillator 24 periodically enables the gate 22 at a relatively high frequency, such as about 40 kHz. Oscillator 28 operates at a substantially lower frequency, on the order of 0.5-5.0 Hz. By adjusting the duration of the one-shot 26 with the power control 21 (FIG. 1), the AND-gate 22 can be disabled for an adjustable period of time, thereby adjusting the duty cycle of the gate 22 and hence the power applied to the tip 14. In summary, when the tip 14 is being heated, amplifier 30' enables AND-gate 22 so that the output of the oscillator 24 is gated to the transformer driver 23. However, AND-gate 22 is periodically disabled at a rate determined by the operating frequency of the oscillator 28.
The tip 14 of the probe 10 is curved in the manner common to dental instruments, and it terminates in a point. However, it will be understood that tips 14 of other shapes can be used. The opposite end of the tip 14 is secured to the probe base 12 by a locking cap 40 threaded onto a plastic fitting 42. A metal, touch-sensitive control button 44 is mounted on the fitting 42. When the practitioner grasps the barrel of the base 12 and touches the button 44, a circuit is completed between the base 12 and button 44 through the on/off sensing switch 32 (FIG. 5) which is boosted by amplifier 30 to enable AND-gate 22. A similar touch-control sensor is described in U.S. Pat. No. 4,177,799, which is incorporated herein by reference. Basically, a voltage is applied between the base 12 and button 44. When the practitioner completes the path between the button 44 and base 12, this flow is detected by the on/off sensing circuit 32 to apply a signal to the amplifier 30'.
One embodiment of the probe tip 14 is shown in FIG. 3. A copper wire 50 runs inside a hollow core 52 of the tip 14. The wire 50 is surrounded by a layer of substantially nonconductive (insulative) material 54, except for a small portion near the leading end 56 of the wire 50. At this leading end 56, a stainless steel outer layer 58 is soldered to the wire 50 to provide an electrical coupling between the wire 50 and the outer layer 52. The outer layer 52 is substantially isolated and disconnected from the wire 50 except at the leading end 56. Current is carried through the wire 50 to the leading end 56, where it enters the outer layer 52. Because the outer layer 52 has a resistance greater than that of the inner wire 50, the outer layer 52 forms a resistive heater for the tip 14. Preferably, the outer layer 52 forms a hollow core so that the cross-sectional area of the outer layer 52 increases as the layer proceeds away from the leading end 56. An outer layer 52 of this nature thus has a generally decreasing current density away from the end 56, and, therefore, provides more heat near the leading end than farther away from the leading end 56. Therefore, the greatest heat may be concentrated at the tip of the instrument probe.
FIG. 4 shows an alternate embodiment of a preferred tip of this invention. The alternate tip 14A includes an aluminum core 60 having an insulation layer 62 fabricated about it. The leading end 64 of the aluminum core 60 has the insulative layer removed from it. At this end, a resistive outer layer 66 is in electrical contact with the core 60. This outer layer 66 is similar to the outer layer 52 of the first embodiment. That is, it is a resistive element which heats up when current passes through the core into the outer layer. It may be shaped to provide concentrated heating near the leading end 64 of the alternate tip 14A. For example, the outer conductive layer 66 may be a metal deposited by vacuum deposition or flame spraying.
Because the method of construction of a tip of the nature shown in FIG. 4 allows for fabrication in nearly any shape, this method may be preferred. That is, the tip can be made by fashioning the core 60 into the desired shape. The core 60 is then processed to provide the insulative layer 62 between the conductive core 60 and resistive outer layer 66. The outer layer 66 may then be deposited upon the insulative layer 62 to make electrical contact with the core 60 at or near the leading end 64. Almost any shape of tip may be employed with this method; and, particularly, very narrow, fine point tips may be fabricated to include an integral resistive heating element. The thickness of the outer layer 66 may be readily controlled to provide the desired heat concentration near the leading end 64 of the tip 14A.
The interface between the tip 14 and probe base 12 is illustrated in FIG. 2 for the tip 14 of FIG. 3. A tubular, electrically conductive collar 70 of brass or the like surrounds and makes electrical contact with the end of the outer layer 36. The end of the collar 70 extends beyond the end of the outer layer 36 to form a cylindrical recess. A conductive tube 72, having a reduced diameter projection 74 surrounded by a layer of insulation 76, fits into the cylindrical recess formed by the collar 70. The outer layer 36 is thus supported from the tube 72, but is electrically insulated from it. The wire 30 extending through the hollow interior of the outer layer 36 extends through a hollow cavity in the tube 72 and is soldered to the end of the tube 72 at 78. The collar 70 and tube 72 thus form contact points for completing a circuit through the outer layer 36 and wire 30. The tube 72 and collar 70 are inserted through the cap 40 into the fitting 42. The collar 70 makes contact with the cap 40 and, from there, to one contact of the transformer 16. The tube 72 abuts a contact in the fitting 42 and is connected to the other terminal of the transformer 16. In this manner, tips 14 can be removed for sterilization and then re-attached to the probe 10 by merely releasing the cap 40 and inserting the substitute tip 14.
While preferred medical or dental probes have been described along with their methods of construction, those skilled in the art will readily recognize modifications that may be made to the embodiments disclosed. For example, the core 60, instead of the outer layer 66, could be fabricated from a resistive material, and vice versa; or the same material could be used in both core 60 and outer layer 66. These modifications are intended to be a part of the invention if they use the underlying concepts of this invention. The claims of this invention should be interpreted to the extent allowable by reference to this description and to the prior art. The preferred embodiments disclosed should be used by way of limitation only to the extent necessary to define the invention. Specifically, the resistive outer layer 52 or 66 may be of uniform cross-sectional area if heat concentration at the tip is not desired. Also, the tip may assume a variety of shapes other than the shape shown herein. For example, a tubular tip may be flattened to a trowel-like configuration and the flattened tip may be formed into a spoon.
|Cited Patent||Filing date||Publication date||Applicant||Title|
|US3698394 *||Jun 14, 1971||Oct 17, 1972||Polak Teodor||Electrically heated hypodermic needle|
|US3886944 *||Nov 19, 1973||Jun 3, 1975||Jamshidi Khosrow||Microcautery device|
|US4074719 *||Jun 24, 1976||Feb 21, 1978||Kurt Semm||Method of and device for causing blood coagulation|
|US4392827 *||Nov 4, 1981||Jul 12, 1983||Howard Martin||Self-contained root canal heated condenser dental instrument|
|Citing Patent||Filing date||Publication date||Applicant||Title|
|US4807596 *||Sep 11, 1986||Feb 28, 1989||Messerschmitt-Bolkow-Blohm Gmbh||Guiding probe|
|US4992045 *||Oct 28, 1988||Feb 12, 1991||Dentsply Research & Development Corp.||Battery powered condenser for root canals|
|US4993946 *||Dec 21, 1989||Feb 19, 1991||Alan Kirsch||Thermal tooth pulp tester|
|US5043560 *||Sep 29, 1989||Aug 27, 1991||Masreliez C Johan||Temperature control of a heated probe|
|US5406053 *||Jul 29, 1993||Apr 11, 1995||Masreliez; C. Johan||Heating probe having a heated tip forming a thermocouple|
|US5421727 *||Jun 7, 1993||Jun 6, 1995||Stevens; Barry H.||Dental instrument with microwave/RF radiation and method of treating a tooth|
|US5554838 *||Aug 23, 1995||Sep 10, 1996||Wind Lock Corporation||Hand-held heating tool with improved heat control|
|US5752825 *||May 24, 1996||May 19, 1998||Buchanan; Leonard Stephen||Endodontic treatment system|
|US5836764 *||May 24, 1996||Nov 17, 1998||Buchanan; Leonard Stephen||Endodontic treatment system|
|US5842861 *||May 24, 1996||Dec 1, 1998||Buchanan; Leonard Stephen||Endodontic treatment system|
|US5893713 *||Dec 4, 1997||Apr 13, 1999||Kerr Manufacturing Company||Dental probe having superelastic plugger element and method of use thereof|
|US5897316 *||Apr 28, 1994||Apr 27, 1999||Buchanan; Leonard Stephen||Endodontic treatment system|
|US5921775 *||May 24, 1996||Jul 13, 1999||Buchanan; Leonard Stephen||Endodontic treatment system|
|US6087631 *||Feb 25, 1999||Jul 11, 2000||Hakko Corporation||Soldering iron with temperature control cycles related to rectified voltage cycles|
|US6106283 *||Jul 22, 1999||Aug 22, 2000||Roffe; Tara||Root canal obturation instrument|
|US6254389||Sep 20, 1999||Jul 3, 2001||Marc Seghatol||Hand-held microwave intra-oral dental system|
|US6270343 *||Jan 7, 2000||Aug 7, 2001||Howard Martin||Endodontic thermal condenser dental instrument|
|US6416320||Aug 18, 2000||Jul 9, 2002||Brian Roffe||Dental instrument for use in root canal obturation|
|US6441354||Sep 20, 1999||Aug 27, 2002||Marc Seghatol||Microwave polymerization system for dentistry|
|US6605651||Sep 8, 1999||Aug 12, 2003||Biomat Sciences, Inc.||Curing methods and material compositions having dental and other applications|
|US6704670 *||Apr 16, 2002||Mar 9, 2004||Agilent Technologies, Inc.||Systems and methods for wideband active probing of devices and circuits in operation|
|US6737619||Jun 10, 2002||May 18, 2004||Marc Seghatol||Microwave polymerization system for dentistry|
|US6891130 *||Apr 7, 2003||May 10, 2005||Walter Evanyk||Appliance for dispensing melt adhesive with variable duty cycle and method of implementing|
|US6948933||Oct 25, 2002||Sep 27, 2005||Suk Song Oh||Complex root canal plugging apparatus for dental work|
|US7004755||Jul 2, 2001||Feb 28, 2006||Marc Seghatol||Hand-held microwave intra-oral dental system|
|US7008222||Jun 24, 2003||Mar 7, 2006||Suk Song Oh||Root canal plugging apparatus for dental work|
|US20030195713 *||Apr 16, 2002||Oct 16, 2003||Mctigue Michael T.||Systems and methods for wideband active probing of devices and circuits in operation|
|US20030205566 *||Apr 7, 2003||Nov 6, 2003||Walter Evanyk||Appliance for dispensing melt adhesive with variable duty cycle and method of implementing|
|US20040009452 *||Oct 25, 2002||Jan 15, 2004||Oh Suk Song||Complex root canal plugging apparatus for dental work|
|US20040265772 *||Jun 24, 2003||Dec 30, 2004||Oh Suk Song||Root canal plugging apparatus for dental work|
|US20050011885 *||Apr 12, 2004||Jan 20, 2005||Marc Seghatol||Hand-held microwave polymerization system for dentistry|
|US20060027553 *||Aug 9, 2004||Feb 9, 2006||Hanisko Francis D||Heater for endodontic condenser|
|US20080179309 *||Jan 25, 2007||Jul 31, 2008||Markovsky Robert T||Soldering Iron with Direct Current Powered Heating Element|
|US20100112512 *||Nov 3, 2009||May 6, 2010||Jones Thomas L||Dental testing device for heat sensitivity|
|US20100124728 *||Nov 11, 2009||May 20, 2010||Harmeet Walia||Device and method for in canal gutta-percha heating and condensation|
|US20100243712 *||Sep 30, 2010||Ats Automation Tooling Systems Inc.||Thermode, clamping arrangment therefor, and method of manufacture|
|USRE39174 *||Apr 26, 2001||Jul 11, 2006||Leonard Stephen Buchanan||Endodontic treatment system|
|EP0285069A1 *||Mar 28, 1988||Oct 5, 1988||Dentsply International, Inc.||Battery powered condenser for root canals|
|WO1991005300A1 *||Sep 27, 1990||Apr 18, 1991||Masreliez C Johan||Temperature control of a heated probe|
|WO2000018191A1 *||Sep 17, 1999||Mar 30, 2000||Marc Seghatol||Microwave polymerization system for dentistry|
|WO2001049202A1 *||Jan 7, 2000||Jul 12, 2001||Marino Borrelli||Endodontic apparatus and method for filling of prepared root canals|
|WO2005067809A1 *||Jan 19, 2004||Jul 28, 2005||Meta Biomed Co., Ltd||Complex root canal plugger for dental clinic|
|WO2005079668A1 *||Feb 16, 2005||Sep 1, 2005||Erskine Products Pty Ltd||Tooth pulp condition probe|
|WO2006020505A1 *||Aug 5, 2005||Feb 23, 2006||Aseptico, Inc.||Heater for endodontic condenser|
|WO2010108284A1 *||Mar 29, 2010||Sep 30, 2010||Ats Automation Tooling Systems Inc.||Thermode, clamping arrangement therefor, and method of manufacture|
|U.S. Classification||606/31, 433/32, 219/233|
|International Classification||A61C5/04, A61B18/08|
|Cooperative Classification||A61C5/04, A61C5/045, A61B18/082|
|European Classification||A61B18/08B, A61C5/04|
|Jan 9, 1989||FPAY||Fee payment|
Year of fee payment: 4
|Aug 3, 1992||FPAY||Fee payment|
Year of fee payment: 8
|Jan 8, 1997||FPAY||Fee payment|
Year of fee payment: 12
|Dec 22, 2000||AS||Assignment|
Owner name: ABN AMRO BANK N.V., ILLINOIS
Free format text: SECURITY INTEREST;ASSIGNOR:ORMCO CORPORATION;REEL/FRAME:011400/0232
Effective date: 20001211
|Jun 13, 2002||AS||Assignment|
Owner name: ORMCO CORPORATION, CALIFORNIA
Free format text: SECURITY INTEREST;ASSIGNOR:ABN MARO BANK N.V.;REEL/FRAME:012946/0993
Effective date: 20020606